EP0452595A1 - Cathéter cristallin liquide et son procédé de fabrication - Google Patents

Cathéter cristallin liquide et son procédé de fabrication Download PDF

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Publication number
EP0452595A1
EP0452595A1 EP90314428A EP90314428A EP0452595A1 EP 0452595 A1 EP0452595 A1 EP 0452595A1 EP 90314428 A EP90314428 A EP 90314428A EP 90314428 A EP90314428 A EP 90314428A EP 0452595 A1 EP0452595 A1 EP 0452595A1
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EP
European Patent Office
Prior art keywords
liquid crystalline
tubing
melt
point
needle
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP90314428A
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German (de)
English (en)
Other versions
EP0452595B1 (fr
Inventor
James M. Lambert
Donald D. Solomon
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Becton Dickinson and Co
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Becton Dickinson and Co
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Filing date
Publication date
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Publication of EP0452595A1 publication Critical patent/EP0452595A1/fr
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Publication of EP0452595B1 publication Critical patent/EP0452595B1/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
    • A61L29/04—Macromolecular materials
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
    • A61L29/14—Materials characterised by their function or physical properties, e.g. lubricating compositions
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/0009—Making of catheters or other medical or surgical tubes
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
    • C08G63/00—Macromolecular compounds obtained by reactions forming a carboxylic ester link in the main chain of the macromolecule
    • C08G63/02—Polyesters derived from hydroxycarboxylic acids or from polycarboxylic acids and polyhydroxy compounds
    • C08G63/60—Polyesters derived from hydroxycarboxylic acids or from polycarboxylic acids and polyhydroxy compounds derived from the reaction of a mixture of hydroxy carboxylic acids, polycarboxylic acids and polyhydroxy compounds
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
    • C08G63/00—Macromolecular compounds obtained by reactions forming a carboxylic ester link in the main chain of the macromolecule
    • C08G63/02—Polyesters derived from hydroxycarboxylic acids or from polycarboxylic acids and polyhydroxy compounds
    • C08G63/60—Polyesters derived from hydroxycarboxylic acids or from polycarboxylic acids and polyhydroxy compounds derived from the reaction of a mixture of hydroxy carboxylic acids, polycarboxylic acids and polyhydroxy compounds
    • C08G63/605—Polyesters derived from hydroxycarboxylic acids or from polycarboxylic acids and polyhydroxy compounds derived from the reaction of a mixture of hydroxy carboxylic acids, polycarboxylic acids and polyhydroxy compounds the hydroxy and carboxylic groups being bound to aromatic rings
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
    • C08L25/00—Compositions of, homopolymers or copolymers of compounds having one or more unsaturated aliphatic radicals, each having only one carbon-to-carbon double bond, and at least one being terminated by an aromatic carbocyclic ring; Compositions of derivatives of such polymers
    • C08L25/02—Homopolymers or copolymers of hydrocarbons
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
    • C08L67/00—Compositions of polyesters obtained by reactions forming a carboxylic ester link in the main chain; Compositions of derivatives of such polymers
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
    • C08L71/00—Compositions of polyethers obtained by reactions forming an ether link in the main chain; Compositions of derivatives of such polymers
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
    • C08L77/00—Compositions of polyamides obtained by reactions forming a carboxylic amide link in the main chain; Compositions of derivatives of such polymers
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
    • C08L83/00—Compositions of macromolecular compounds obtained by reactions forming in the main chain of the macromolecule a linkage containing silicon with or without sulfur, nitrogen, oxygen or carbon only; Compositions of derivatives of such polymers
    • C08L83/04—Polysiloxanes
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
    • C08L85/00—Compositions of macromolecular compounds obtained by reactions forming a linkage in the main chain of the macromolecule containing atoms other than silicon, sulfur, nitrogen, oxygen and carbon; Compositions of derivatives of such polymers
    • C08L85/02—Compositions of macromolecular compounds obtained by reactions forming a linkage in the main chain of the macromolecule containing atoms other than silicon, sulfur, nitrogen, oxygen and carbon; Compositions of derivatives of such polymers containing phosphorus
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
    • B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
    • B29C45/00—Injection moulding, i.e. forcing the required volume of moulding material through a nozzle into a closed mould; Apparatus therefor
    • B29C2045/0098—Injection moulding, i.e. forcing the required volume of moulding material through a nozzle into a closed mould; Apparatus therefor shearing of the moulding material, e.g. for obtaining molecular orientation or reducing the viscosity

Definitions

  • This invention relates to a plastic medical article and more particularly relates to a catheter of improved mechanical properties.
  • liquid crystals Substances which exhibit physical properties characteristic of a transition state between conventional liquids and solid are generally termed liquid crystals.
  • the transition state is believed to be a result of an ordering of the molecules in melts and solutions of various organic compounds that occurs within certain ranges of temperature. The ordering is sufficient to impart some solid-like properties to the substances, but the forces of attraction usually are not strong enough to prevent flow.
  • liquid crystallinity or the synonymous term mesomorphism.
  • Catheterization procedures conventionally include puncture of a patient's skin and insertion of a catheter into a body cavity, such as the blood stream, using some type of catheter insertion device.
  • the puncturing tip be as sharp as possible.
  • the catheter, and perforce any insertion equipment be of the smallest possible cross-sectional area during insertion and use.
  • the catheter lumen must be large enough to achieve the required rate of administration of a medicament solution through the catheter.
  • catheters are of great length and are extended along rather tortuous and extended paths within the body to reach desired locations. Accordingly, the ideal catheter would be stiff enough for insertion and manipulation inside a vein or artery without kinking, but at the same time be sufficiently soft and nonbrittle to avoid breaking off.
  • Catheters of the prior art have generally been made of polymeric materials such as polystyrene, polycarbonate, polyurethane and polyacrylate. These materials, while providing advantages for certain catheter applications, nevertheless have mechanical properties which limit their use for other applications. Accordingly, there is a need for a catheter having a balance of strength, stiffness and nonbrittleness suitable for insertion into a patient and maneuverability after insertion.
  • the present invention addresses this need.
  • a catheter assembly includes a tubing portion and a needle portion for penetration of a patient's skin, at least one of the tubing and needle portions being of a thermoplastic liquid crystalline polymer.
  • the tubing and needle portions may be a single integral liquid crystalline catheter molded to include a point, and the tubing portion may include a hub portion.
  • the needle portion may be a metal needle affixed to the liquid crystalline tubing, or it may be a liquid crystalline needle having a point affixed to a tubing of either liquid crystalline polymer or non-liquid crystalline polymer.
  • thermotropic liquid crystalline polymer which undergoes molecular orientation on shear thinning and retains the orientation on cooling may be extruded into the tubing of the invention.
  • shear thinning describes the well-known propensity of most polymer melt to undergo reduction in viscosity when subjected to conditions of high shear.
  • Preferred liquid crystalline polymers shear-thin to a viscosity of 500 poise or less and thereby flow into and fill completely the point of a hollow needle mold.
  • Most preferred are liquid crystalline polyesters.
  • the invention includes a method to prepare tubing by extruding shear thinned liquid crystalline polymers and a method to prepare hollow needles and catheters having a point by passing a melt of liquid crystalline polymer through an orifice to effect shear thinning and directing the shear thinned melt into a hollow tubing mold which has a point.
  • Molecularly oriented liquid crystalline polymers have high impact strength, high flex or bend modulus and low elongation. These properties make them admirably suited for fabrication into plastic articles having a point for skin penetration without danger of bending or breaking. Further, the pointed articles can be made in a single molding operation because melts of the polymers shear thin to a viscosity low enough to flow into and completely fill a mold including a point.
  • a particularly useful article is a tubing having a molded point which may serve as a catheter without the need for a separate catheter inserter.
  • the catheter tubing of the invention may be of very thin wall so that a lumen large enough to provide adequate fluid flow can be obtained in a catheter of narrow outside diameter for patient comfort. Because the wall is thin, the high flex modulus is overcome sufficiently to allow the catheter to be threaded through tortuous pathways without breaking, kinking or needing a guide wire.
  • Liquid crystalline polymers have some radiopaquing properties for visualization after insertion, but also are compatible with conventional radiopaque agents, such as bismuth oxide, for formulations of higher radiopaque visibility.
  • a catheter which is at least partially fabricated of a liquid crystalline polymer comprises a tubing open at both ends.
  • the catheter may include a point for penetration of a patient's skin.
  • the tubing may be entirely of a liquid crystalline polymer molded to include a point so that a separate catheter inserter is not needed.
  • a liquid crystalline polymeric tubing may be used with a separate needle portion which includes the point.
  • the needle may be a conventional stainless steel needle or may be of the same or a different liquid crystalline polymer.
  • a liquid crystalline polymeric needle may be used with a tubing of a non-liquid crystalline polymer.
  • One embodiment of the invention illustrated in Figs. 1 and 2, includes a tubing 10 having a first open end 12 for connection to, for example, a medicament reservoir (not shown).
  • Tubing 10 tapers to a point 14, preferably beveled, and also has a second open end 16.
  • Tubing 10 defines a lumen 18 as illustrated in Fig. 2.
  • FIGs. 3 and 4 illustrate a catheter of polymeric tubing 10a having open end 12a.
  • Tubing 10a is affixed to a needle 20 having open end 16a and point 14a, preferably beveled.
  • Tubing 10a and needle 20 define a lumen 18a.
  • the liquid crystalline polymeric tubing may be connected to a hub.
  • the hub and tubing may be separate components conventionally attached, as by glue, wherein the hub may be of the same or different liquid crystalline polymer or the hub may be of a non-liquid crystalline polymer.
  • the hub and tubing are integrally molded of liquid crystalline polymer.
  • Fig. 5 and 6 show liquid crystalline tubing 10b integrally molded with hub 30.
  • Hub 30 has a passageway 32 therethrough which provides fluid communication between tubing 10b and a needle 20b.
  • hub 30 is shown to be conical, it may be of any shape convenient for conventional attachment to needle 20b and may include other integrally molded parts, such as tabs, lugs or threads (not shown) which may be useful for attachment to the needle.
  • the hub may also include an optional port 36 and associated projection 38 for attaching a second tubing (not shown).
  • gluing may be used for attaching separate needle and tubing components.
  • the needle is inserted inside of the tubing by an interference fit.
  • thermoplastic polymer of elongated molecular shape which can exist in a liquid crystalline phase is contemplated to fall within the scope of this invention.
  • polymer classes which can form liquid crystals are polyethers, polyphosphazines polyxylylenes, polysulfones, polyamides, polysiloxanes and polyesters.
  • Preferred liquid crystalline polymers for molding into the catheter of the invention are polyesters having a plurality of aromatic rings which contribute to ordering or alignment of the elongated molecules. The aromatic rings may be connected directly together, as in biphenyl moieties, or they may be separated by a connecting unit, as exemplified by generic structures I and II.
  • Ar1 and Ar3 may be an aromatic, heterocyclic or substituted aromatic ring such as phenyl, pyridyl, naphthyl, biphenyl or quinolyl wherein the substituent may be a halogen or lower alkyl group.
  • a and B may be alkyl, alkyloxy, alkyldioxy, oxygen, sulfur, sulfone, carbonyl, oxycarbonyl, alkylcarbonyl, alkyloxycarbonyl, alkylcarbonyloxy and oxyalkylcarbonyl wherein at least one of A and B is an oxycarbonyl group, the term alkyl being about 1 to 5 carbon atoms, X and Y may be hydroxyl or carboxyl and groups X,Y,A and B may be in a meta or para relationship or, if Ar is a naphthylene or quinoline ring, the bonds to A and B may be in a 2,6; 2,7; 3,6; 3,7; or 4,8 relationship.
  • liquid crystalline polymers suitable for the present invention are commercially available, such as VectraTM (Hoechst-Celanese, Chatham, New Jersey, XydarTM and TorlonTM (Amoco Performance Products, Ridgefield, Connecticut, and LCPTM (RTP Co., Winona, Minnesota).
  • VectraTM Hoechst-Celanese, Chatham, New Jersey
  • XydarTM XydarTM
  • TorlonTM Amoco Performance Products, Ridgefield, Connecticut
  • LCPTM RTP Co., Winona, Minnesota
  • Synthesis of the preferred crystalline polyesters used in the invention may be carried out by well-known esterification and transesterification procedures.
  • hydroxyaromatic acids such as hydroxy benzoic acid, hydroxynaphthoic acid and hydroxybiphenyl carboxylic acid may be polymerized or copolymerized.
  • Aromatic dicarboxylic acids such as terephthalic acid, isophthalic acid, naphthylene dicarboxylic acid and biphenyl dicarboxylic acid may be polymerized with aromatic glycols, such as dihydroxybenzene, dihydroxynaphthylene and dihydroxybiphenyl, araliphatic glycols, such as p-hydroxy benzyl alcohol, or with aliphatic glycols, such as ethylene glycol.
  • Aliphatic dicarboxylic acids, such as succinic acid may be polymerized with aromatic glycols such as hydroquinone.
  • melts of polymeric liquid crystallines are known to have a degree of molecular organization whereas melts of ordinary polymers exist in an almost completely random state. Organization of the molecules of both ordinary polymers and liquid crystalline polymers is greatly enhanced by shear thinning. As is known in the art, shear thinning is due to orientation of the elongated polymer molecules into an arrangement in which the molecules are aligned substantially completely in the direction of melt flow through an orifice. While most polymers undergo more or less shear thinning, conventional polymers such as polypropylene or polyethylene do not retain their orientation on cooling, but rather undergo molecular randomization and thereby lose the mechanical properties gained when their melts are shear thinned.
  • a shear thinned liquid crystalline polymer melt having filled a mold, retains its molecular orientation on cooling, and it is the oriented molecules in the cooled polymer which gives the molded product the unique combination of properties characteristic of liquid crystalline polymers.
  • the catheter tubing of the invention may have a gauge size of from 8 to 26.
  • Preferred tubing is of 14 to 20 gauge.
  • the invention includes a hollow plastic article having a point sufficiently sharp to penetrate a patient's skin without substantial discomfort.
  • Preferred hollow articles are catheters and needles which may have a point of any desired shape.
  • the most preferred hollow article is a catheter which has a beveled point for maximum patient comfort, it is evident that a hollow plastic needle may also find application in a variety of other areas, such as liquid transfer for example with a hypodermic needle attached to a syringe.
  • a particularly attractive application of liquid crystalline needles is in magnetic resonance imaging (MRI), a non-invasive diagnostic technique which uses apparatus which includes a very high field magnet. Oftentimes needles which must be nonmetallic are used to biopsy areas highlighted by the MRI.
  • MRI magnetic resonance imaging
  • suitable polymers are, for example, polypropylene, polytetrafluoroethylene, polyurethane, polyethylene terephthalate and the like.
  • liquid crystalline polymers after extruding into tubing or molding into hollow needles have high impact strength.
  • the tensile at break of the molded or extruded liquid crystalline polymer may be about 10,000 to 70,000 psi, preferably about 25,000 to 35,000 psi.
  • Elongation at break may be about 1 to 50, preferably about 2 to 10%.
  • the flex modulus may be about 1,000,000 to 20,000,000, preferably about 3,000,000 to 7,000,000 psi. For polystyrene, a product totally unsuitable because of its brittleness, these values are about 6,000 psi, 2% and 480,000 psi respectively.
  • liquid crystalline polymer melt is suitable for molding into the inventive devices having a sharp point if it has a viscosity of no more than about 500 poise.
  • Preferred liquid crystalline polymers have a shear-thinned viscosity of about 75 to 150 poise.
  • Such products have a very low coefficient of friction, generally in the range of 0.1 to 0.25. This property enables the article of the invention to release from the mold without any mold releasing agents.
  • the catheter tubing of the invention may be fabricated from a thermoplastic liquid crystalline polymer by conventional means.
  • a mandrel may be alternately dipped into a melt or solvent solution of the polymer and dried, the process being repeated until the tubing is of the desired thickness.
  • a preferred method for forming a tubing is by conventional melt and solution extrusion processes well-known to one skilled in the art wherein shear thinning takes place when the melt or solution passes through the extrusion die.
  • a liquid crystalline homopolymer may be extruded, or a solution or melt of a mixture of liquid crystalline polymers may be extruded.
  • two or more polymers may be coextruded using conventional equipment giving a tubing having a base layer and one or more laminated layers. Such a tubing may present different surfaces to the body environment and any liquid passing through the tubing.
  • a method to prepare hollow liquid crystalline polymeric needles includes melting a thermotropic liquid crystalline polymer and introducing the melt into an injection mold of the desired shape in a conventional molding operation. Molding may be performed at any temperature between the melting and decomposition temperatures of the polymer at which the viscosity of the melt is sufficiently low to enable the melt to completely fill the mold.
  • the polymer may be melted to its anisotropic melt range and processed while within this range.
  • the polymer melt may be forced under pressure through an orifice and thence directly into the mold. Passage of the melt through the orifice effects shear thinning and reduces the viscosity of the melt to facilitate completely filling of the mold.
  • the degree of shear thinning of a polymer is a function of the nature of the polymer, the temperature, the pressure applied (and thus the rate of passage through the orifice) and the size of the orifice. These variables are well-known in the injection molding art, and a suitable combination of thinning and molding conditions may easily be determined by those skilled in the art. Thus, without wishing to be limited thereby, suitable molding parameter ranges are a pressure of 500 to 1,500 psi, a shear rate of 10 to 150 sec ⁇ 1 , and an orifice size of 0.5 to 2.0 mm. After shear thinning, the polymer melt flows into and completely fills the mold, including the tip.
  • the molded point of the article is generally sharp enough to puncture a patient's skin without substantial discomfort.
  • the molded point may be machined by any conventional procedure such as grinding or sanding, or may be thermoformed in a heated tipping die to further sharpen the point.
  • the finished article may then be sterilized by any convenient procedure, such as heat, irradiation, or chemical methods taking advantage of the known stability of liquid crystalline polymers to these techniques.
  • the low friction surface of the point of the article of the invention in many cases allows skin puncture without any lubricant.
  • conventional stainless steel needles have a coefficient of friction of about 0.57, and often are lubricated prior to puncture of a patient's skin, as, for example, with a polysiloxane lubricant.
  • Polyester liquid crystalline polymer (Vectra®) was melted and forced at a temperature of 290°C under a pressure of 900 psi through a die having a circular orifice of 1.6 mm diameter.
  • the die was mounted on a conventional injection molding apparatus so that the polymer, after passing through the orifice, flowed directly into a tubing mold shaped to include a beveled point. After filling, the mold was cooled and the tubing was removed. It was found that the tubing had a point which was comparable in penetration force to a stainless steel lancet (Becton, Dickinson and Company).

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  • Chemical & Material Sciences (AREA)
  • Health & Medical Sciences (AREA)
  • Organic Chemistry (AREA)
  • Polymers & Plastics (AREA)
  • Medicinal Chemistry (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Veterinary Medicine (AREA)
  • Animal Behavior & Ethology (AREA)
  • Public Health (AREA)
  • Epidemiology (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Hematology (AREA)
  • Engineering & Computer Science (AREA)
  • Pulmonology (AREA)
  • Biophysics (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Materials For Medical Uses (AREA)
  • Media Introduction/Drainage Providing Device (AREA)
EP90314428A 1990-03-19 1990-12-28 Cathéter cristallin liquide et son procédé de fabrication Expired - Lifetime EP0452595B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US07/495,072 US5078700A (en) 1990-03-19 1990-03-19 Liquid crystalline catheter
US495072 1990-03-19

Publications (2)

Publication Number Publication Date
EP0452595A1 true EP0452595A1 (fr) 1991-10-23
EP0452595B1 EP0452595B1 (fr) 1995-08-23

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Family Applications (1)

Application Number Title Priority Date Filing Date
EP90314428A Expired - Lifetime EP0452595B1 (fr) 1990-03-19 1990-12-28 Cathéter cristallin liquide et son procédé de fabrication

Country Status (10)

Country Link
US (1) US5078700A (fr)
EP (1) EP0452595B1 (fr)
JP (1) JPH04221570A (fr)
AT (1) ATE126713T1 (fr)
AU (1) AU632389B2 (fr)
CA (1) CA2031696A1 (fr)
DE (1) DE69021866D1 (fr)
ES (1) ES2078953T3 (fr)
IE (1) IE904407A1 (fr)
NZ (1) NZ236403A (fr)

Cited By (12)

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Publication number Priority date Publication date Assignee Title
EP0646357A1 (fr) * 1993-09-30 1995-04-05 Ethicon, Inc. Instrument chirurgical avec moyens améliorés pour manipuler
EP0652025A1 (fr) * 1993-09-10 1995-05-10 Critikon, Inc. Procédé pour fixer de façon étanche l'extrémité d'un cathéter à une aiguille d'introduction
EP0652023A2 (fr) * 1993-09-10 1995-05-10 Critikon, Inc. Aiguille de cathéter avec une indication sur sa surface et procédé pour former ce cathéter
EP0652024A1 (fr) * 1993-09-10 1995-05-10 Critikon, Inc. Procédé de biseautage avec laser pour cathéters
WO1996003162A1 (fr) * 1994-07-25 1996-02-08 Advanced Cardiovascular Systems, Inc. Sonde intraluminale dotee d'un axe proximal a haute resistance
EP0826387A2 (fr) * 1996-08-27 1998-03-04 JOHNSON & JOHNSON MEDICAL, INC. Structure revêtue monobloc de cathéter et canule en plastique
WO2000072901A1 (fr) * 1999-05-28 2000-12-07 Novo Nordisk A/S Procede et systeme de production d'une aiguille en plastique
US6942648B2 (en) 1999-12-09 2005-09-13 Advanced Cardiovascular Systems, Inc. Catheter with a transparent shaft
US7744574B2 (en) 2004-12-16 2010-06-29 Boston Scientific Scimed, Inc. Catheter tip to reduce wire lock
US7744586B2 (en) 1997-10-15 2010-06-29 Boston Scientific Scimed, Inc. Catheter with spiral cut transition member
EP2238998A1 (fr) 2009-04-02 2010-10-13 F. Hoffmann-La Roche AG Canule pour percer le septum d'une cartouche et valvule pour la canule
USD1048792S1 (en) 2023-04-12 2024-10-29 Sharkninja Operating Llc Coffee machine

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Publication number Priority date Publication date Assignee Title
AU648387B2 (en) * 1991-03-04 1994-04-21 Medex, Inc. Use of surfactants to improve intravenous catheter flashback
US5188605A (en) * 1991-05-08 1993-02-23 Cordis Corporation Separable insertion tool
US5256149A (en) * 1992-02-14 1993-10-26 Ethicon, Inc. Trocar having transparent cannula and method of using
CA2129651C (fr) * 1992-02-24 2005-12-27 Jaime Ernesto Siman Alliages de polymeres a transmission de couple amelioree, utilises pour la fabrication de catheters
US5387197A (en) * 1993-02-25 1995-02-07 Ethicon, Inc. Trocar safety shield locking mechanism
NL1006254C2 (nl) * 1997-06-06 1998-12-08 Cordis Europ Met MRI-verenigbare geleidingsdraad.
US6517515B1 (en) 1998-03-04 2003-02-11 Scimed Life Systems, Inc. Catheter having variable size guide wire lumen
US8079982B1 (en) 1998-06-04 2011-12-20 Biosense Webster, Inc. Injection catheter with needle electrode
US6905476B2 (en) * 1998-06-04 2005-06-14 Biosense Webster, Inc. Catheter with injection needle
US7416547B2 (en) 1999-03-29 2008-08-26 Biosense Webster Inc. Injection catheter
US6540725B1 (en) * 1998-06-04 2003-04-01 Biosense Webster, Inc. Injection catheter with controllably extendable injection needle
US6368316B1 (en) * 1998-06-11 2002-04-09 Target Therapeutics, Inc. Catheter with composite stiffener
US6936053B1 (en) * 1998-07-02 2005-08-30 Jeffrey N. Weiss Ocular implant needle
US6443925B1 (en) 1999-09-13 2002-09-03 Advanced Cardiovascular Systems, Inc. Balloon catheter shaft formed of liquid crystal polymeric material blend
US6325780B1 (en) 1999-09-13 2001-12-04 Advanced Cardiovascular Systems, Inc. Inflatable member formed of liquid crystal polymeric material blend
US6623504B2 (en) 2000-12-08 2003-09-23 Scimed Life Systems, Inc. Balloon catheter with radiopaque distal tip
JP2002336355A (ja) * 2001-05-11 2002-11-26 Mitsubishi Pencil Co Ltd 注射器針
US20030208142A1 (en) * 2001-06-12 2003-11-06 Boudewijn Alexander C Vascular guidewire for magnetic resonance and /or fluoroscopy
US6749792B2 (en) * 2001-07-09 2004-06-15 Lifescan, Inc. Micro-needles and methods of manufacture and use thereof
US20070066934A1 (en) * 2005-09-19 2007-03-22 Transport Pharmaceuticals, Inc. Electrokinetic delivery system and methods therefor
US20070185432A1 (en) * 2005-09-19 2007-08-09 Transport Pharmaceuticals, Inc. Electrokinetic system and method for delivering methotrexate
US20090318833A1 (en) * 2006-09-18 2009-12-24 Agency For Science Technology And Research Needle Structures and Methods for Fabricating Needle Structures
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EP0652025A1 (fr) * 1993-09-10 1995-05-10 Critikon, Inc. Procédé pour fixer de façon étanche l'extrémité d'un cathéter à une aiguille d'introduction
EP0652023A2 (fr) * 1993-09-10 1995-05-10 Critikon, Inc. Aiguille de cathéter avec une indication sur sa surface et procédé pour former ce cathéter
EP0652024A1 (fr) * 1993-09-10 1995-05-10 Critikon, Inc. Procédé de biseautage avec laser pour cathéters
EP0652023A3 (fr) * 1993-09-10 1995-06-07 Critikon, Inc. Aiguille de cathéter avec une indication sur sa surface et procédé pour former ce cathéter
EP0646357A1 (fr) * 1993-09-30 1995-04-05 Ethicon, Inc. Instrument chirurgical avec moyens améliorés pour manipuler
WO1996003162A1 (fr) * 1994-07-25 1996-02-08 Advanced Cardiovascular Systems, Inc. Sonde intraluminale dotee d'un axe proximal a haute resistance
US5554121A (en) * 1994-07-25 1996-09-10 Advanced Cardiovascular Systems, Inc. Intraluminal catheter with high strength proximal shaft
AU736956B2 (en) * 1996-08-27 2001-08-09 Medex, Inc. Coated one-piece composite plastic catheter and cannula
EP0826387A3 (fr) * 1996-08-27 1998-08-19 JOHNSON & JOHNSON MEDICAL, INC. Structure revêtue monobloc de cathéter et canule en plastique
EP0826387A2 (fr) * 1996-08-27 1998-03-04 JOHNSON & JOHNSON MEDICAL, INC. Structure revêtue monobloc de cathéter et canule en plastique
KR100499737B1 (ko) * 1996-08-27 2005-09-14 죤슨 앤드 죤슨 메디칼 인코포레이티드 피복된플라스틱카테터및캐뉼러의일체식합성체
US7744586B2 (en) 1997-10-15 2010-06-29 Boston Scientific Scimed, Inc. Catheter with spiral cut transition member
WO2000072901A1 (fr) * 1999-05-28 2000-12-07 Novo Nordisk A/S Procede et systeme de production d'une aiguille en plastique
EP1595563A1 (fr) * 1999-05-28 2005-11-16 Novo Nordisk A/S Aiguille en plastique et procédé et système de production d'une aiguille en plastique
US6942648B2 (en) 1999-12-09 2005-09-13 Advanced Cardiovascular Systems, Inc. Catheter with a transparent shaft
US7641838B2 (en) 1999-12-09 2010-01-05 Advanced Cardiovascular Systems, Inc. Catheter with a transparent shaft
US7744574B2 (en) 2004-12-16 2010-06-29 Boston Scientific Scimed, Inc. Catheter tip to reduce wire lock
EP2238998A1 (fr) 2009-04-02 2010-10-13 F. Hoffmann-La Roche AG Canule pour percer le septum d'une cartouche et valvule pour la canule
USD1048792S1 (en) 2023-04-12 2024-10-29 Sharkninja Operating Llc Coffee machine
USD1048793S1 (en) 2023-05-02 2024-10-29 Sharkninja Operating Llc Coffee machine

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US5078700A (en) 1992-01-07
NZ236403A (en) 1993-12-23
AU6794990A (en) 1991-09-19
EP0452595B1 (fr) 1995-08-23
JPH04221570A (ja) 1992-08-12
IE904407A1 (en) 1991-09-25
ES2078953T3 (es) 1996-01-01
DE69021866D1 (de) 1995-09-28
AU632389B2 (en) 1992-12-24
CA2031696A1 (fr) 1991-09-20
ATE126713T1 (de) 1995-09-15

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